Compositions and methods for hemostasis

ABSTRACT

The present invention relates to water soluble and completely absorbable and/or physiologically degradable hemostatic compositions having a wax or wax-like base effective for tamponade hemostasis of bone or cartilage.

RELATED APPLICATIONS

This application claims the benefit of U.S. Provisional Application No.61/554,020, filed Nov. 1, 2011, which is incorporated by reference her,in its entirety.

FIELD OF THE INVENTION

The present invention relates to compositions for use in medical andsurgical procedures to control tissue bleeding from dense tissues suchas bone or cartilage, and, in particular, as hemostatic tamponades.

BACKGROUND OF THE INVENTION

A number of different base materials have been described for themanufacture of compositions intended to achieve hemostasis on bleedingtissue. Many of these are suitable for soft tissues. For example, U.S.Pat. No. 6,060,461 describes porous particles of a polysaccharide,preferably cross-linked dextran, to promote blood clotting on softtissue. The particles, as described, are “designed to act as a sieve todehydrate the blood and accelerate the natural blood clotting process,”US 2009/0062233 describes a hemostat in powder form based on modifiedstarch. U.S. Pat. No. 6,056,970 describes a polysaccharide-based matrixcombined with a fibrin glue or a collagen patch containing, e.g.,aprotinin, fibrinogen, and/or thrombin. U.S. Pat. No. 6,923,961describes hemostatic compositions of derivatized CMC/polyethylene oxide(PEO) composites containing chemical hemostatic agents such as thrombin.

For use in bone, a hemostatic tamponade must adhere to the hard, moistsurface of bleeding bone or cartilage while not adhering appreciably tosurgical gloves and instruments. The composition must also besufficiently moldable for easy application to the site. Optimalformulations are able to withstand the force of saline irrigation thataccompanies typical surgical procedures. The durability of thecomposition in the in vivo environment should be sufficient for thecomposition to serve as an effective hemostatic tamponade at the woundsite throughout the entire intraoperative period and for a sufficienttime after surgery to ensure bleeding has stopped. The term “tamponade”refers to the mechanical hemostasis occurring when a material is appliedto a bleeding surface to occlude the vessels or pores through whichblood flows, creating a static interface between the material and thedammed blood flow. Normal clotting can then occur within this staticinterface. Compositions unsuitable for use as a tamponade do not adheredirectly to the bleeding are easily dislodged by the force of flowingblood or surgical irrigation, or are too water-soluble.

The traditional and still widely used composition for tampanadehemostasis of hone or cartilage is bone wax. Bone wax is generally madefrom beeswax and a softening agent such as iospropyl palmitate. Its maindisadvantage is that it is nondegradable and nonabsorbable underphysiological conditions. This results in undesirable effects such asinhibition of bone healing and osteogenesis and, as with anynonabsorbable foreign body implant, promoting infection, inflammation,and pain.

Several absorbable or partially absorbable alternatives to traditionalbone waxes have been described. For example, U.S. Pat. No. 4,568,536, byKronenthal, et al., and U.S. Pat. No. 4,439,420 by Mattei, et al.,describe compositions featuring particulate solid materials suspended inoils and highly water soluble solid poloxamers (ie Pluronics). U.S. Pat.No. 7,989,000 by Kronenthal describes compositions containing a solidparticulate fatty acid salt suspended in a liquid poloxamer along withcertain other excipients. U.S. Pat. No. 5,356,629 by Sander, et al.,describes a composition containing coated particles ofpolymethylmethacrylate in a matrix of cellulose ether, collagen, orhyaluronic acid. U.S. Pat. No. 7,553,913 and U.S. Pat. No. 7,829,616 byWeilisz, et al., describe hydrophilic water soluble waxy compositionscomprising a base of a random copolymer comprising ethylene oxide andone or more other alkylene oxide(s) which may be mixed with solidparticles. U.S. Pat. No. 7,914,819 by Wen, et al., describes a polymericmatrix having a polysaccharide backbone. U.S. Pat. No. 7,074,425 byConstantine, et al., describes hydrophilic polyethylene glycol basedcompositions consisting of fixture of a high and a low molecular weightpolyethylene glycol of HLB (hydrophilic lipophilic balance) greater than20.

Despite the progress that has been made in this field, there remains aneed for an alternative to “bone wax” that is as effective in achievingtamponade hemostasis for a suitable time while also being completelybiodegradable or absorbable. Water-soluble wax-like compositionsdescribed by e.g., Wellisz (including the commercially available OSTENE)suffer from the disadvantage of not being durable under surgicalconditions to maintain adequate hemostasis for a sufficient period oftime. See, e.g., Holman, 2007. With the exception of traditional honewax, water-insoluble waxes have not generally been utilized in thepreparation of hemostatic tamponades because of their insolubility inthe aqueous in vivo environment and their inability to be phagocytized.

The present invention overcomes these disadvantages by providingcompositions based upon water-soluble wax-like substances that areformulated to maximize their durability under surgical conditions whilemaintaining optimal absorbability and/or degradability underphysiological conditions.

SUMMARY OF THE INVENTION

The present invention provides a hemostatic composition of putty-likeconsistency effective for tamponade hemostasis of bone or cartilagecomprising a freely water soluble (FWS) non-particulate solid basematerial and a dissolution retardant or a dispersion accelerant, whereinthe time to complete dissolution or dispersion of the composition invitro is at least 10 times greater than a reference formulation thatconsists of PEG 1450/PEG 400 90%/10% by weight.

In some embodiments the FWS non-particulate solid base materialsurfactant having an HLB less than 20.

In additional embodiments the FWS non-particulate solid base materialmay be a surfactant having a molecular weight of at least 4000kilodaltons (kD), and may further comprise a softener.

In some embodiments, the invention may further comprise a microporousparticulate ceramic material embedded within solid base material and arapidly hydrating polysaccharide.

In additional embodiments, the macroporous particulate ceramic materialof the current invention may be present in an amount that may be lessthan about 60% by weight of the putty and the polysaccharide may bepresent in an amount that is up to 15% by weight of the putty.

In some embodiments, the invention may further comprise polypropyleneoxide.

The invention further provides a hemostatic composition, which maycomprise an absorbent particulate, wherein when the composition may beexposed to water the rate of water absorption in the first hour may beequal to or exceeds the dissolution of the solid surfactant.

In some embodiments, the invention may further comprise a waterabsorbing dissolution retardant.

In one embodiment, provides a hemostatic composition of putty-likeconsistency effective tamponade hemostasis of bone or cartilage, whichcomprises a poorly water soluble (PWS) non-particulate solid basematerial and a dispersion accelerant, where the PWS base material may bea water insoluble wax-like material.

In one embodiment, the invention provides bone substitute composition,which comprises a rounded, microporous, particulate ceramic suspended ina non-particulate water soluble base.

In some embodiments the bone substitute is a hand moldable bonesubstitute comprising a solid surfactant and less than 70% by weight ofa biphasic microporous calcium phosphate in the form of rounded granuleswherein said granules have a density greater than 2.5.

BRIEF DESCRIPTION OF THE FIGURES

FIGS. 1A-B: Graphs of the dissolution kinetics of two compositionsderived using the biopsy bag method (see specification for details). (A)OSTENE, a mixture of water-soluble alkylene oxide block copolymers(derived from ethylene oxide and propylene oxide) and a random copolymerof polyethylene and polypropylene glycols undergoes complete dissolutionin about 105 minutes at 37° C. (B) PEG 1450/400 (“PEG referenceformulation”), a mixture of polyethylene glycols of different molecularweights undergoes complete dissolution in less than 10 minutes.

FIGS. 2A-B: (A) A graph of the dissolution kinetics of representativeinventive compositions compared to the two reference materials in FIG. 1(Ostene & PEG1450/400) All formulations exceed the dissolution time ofthe reference materials. (B) A graph of the dissolution kinetics ofaddition of the inventive compositions. Dissolution was analysed by thebiopsy bag method. (see specification for method details).

FIG. 3: Dissolution kinetics of representative inventive compositions.Samples were prepared as described for FIG. 2. Dissolution kinetics weredetermined by the mesh basket method (see specification for methoddetails).

FIG. 4: Dissolution kinetics of representative inventive compositions.Samples were prepared as described in FIG. 2. Dissolution kinetics weredetermined by the mesh basket method (see specification for methoddetails).

FIGS. 5A-B: FIG. 5A shows a bar graph of the effect of time on thedissolution or water uptake and the percentage of mass. FIG. 5B shows abar graph on the effect of time on the dissolution or water uptake onthe percentage rate.

FIG. 6: In vivo absorption time of the inventive compositions comparedto controls. Product implanted in 3 mm holes in the rabbit femur.

DETAILED DESCRIPTION OF TUE INVENTION

The compositions of the invention control blood loss from bleedingtissue including hone or cartilage surfaces and, optionally, provide ameans for the controlled release of one or more therapeutic agents andsupport of hone and tissue growth at the site of application. In certainembodiments, the compositions of the invention also serve to fill a voidor gap in bone or cartilage. The compositions of the invention aresuperior to certain other bone waxes in their enhanced durability undersurgical conditions as evidenced by their ability to maintain tamponadehemostasis at the site of application for at least 3 hours andpreferably for at least about 6 or at least about 8 hours.

The compositions of the invention are formed from a mixture comprisingnon-particulate solid that is either freely water soluble (FWS) orpoorly water-soluble/insoluble (PWS). The FWS and PWS non-particulatesolids (formulation bases) used to form the compositions of theinvention are generally wax or wax-like solids under ambient conditions.The term “wax”, as used herein, refers to both water-soluble andwater-insoluble waxes and wax-like solids. A wax, according to theinvention, is a solid at room temperature and generally has a meltingpoint above 30° C., preferably above 40° C., and most preferred above45° C. Water-soluble waxes suitable for use in the compositions of theinvention include, for example, water soluble poly(oxiranes), orpoly(alkylene oxides), water-soluble esters of fatty acids (such asphospholipids), and ethoxylated fatty acids (such as PEG stearates andPoloxamer stearates). Thus, a wax-like solid in this context, isphysically, but not necessarily chemically, similar to a traditional wax(a solid ester of a fatty acid and a fatty alcohol) or a solid paraffinof suitable molecular weight.

The compositions of the invention are able to maintain tamponadehemostasis at the site of application for suitable periods of time. Theinvention provides in vitro methods for screening the inventivecompositions relative to formulations already existing in the art. ForFWS compositions, these screening methods allow the identification offormulations that dissolve more slowly than previous formulations of theart, and the development of new formulations with better intraoperativehemostatic reliability, with less rebleeding than observed with theexisting compositions of the art. For PWS formulations, which areexpected to have excellent intraoperative hemostatic reliability, the invitro assays allow the determination of appropriately active dispersionaccelerators. Preferably, the compositions of the invention are able tomaintain hemostasis in such an assay for at least 15 minutes, at least30 minutes, at least 90 minutes, at least 120 minutes, or for from about30 to 60 minutes or 60 to 120 minutes, 90 to 120 minutes, 120 to 180minutes, 180 to 240 minutes, or longer.

In certain embodiments, the compositions of the invention are able tomaintain tamponade hemostasis intraoperatively and postoperatively atthe site of application for periods of time including 1.5 to 3 hours, 3to 6 hours, 6 to 9 hours, or 9 to 12 hours without appreciablere-bleeding or the need for reapplication of the material. In certainembodiments, the hemostasis efficacy of the compositions is measuredwith an in vivo assay, for example, using living rabbit hone asdescribed herein.

Following implantation in the body, the compositions of the inventionare eliminated from, absorbed or degraded in, the body in up to about 1to 2 weeks. In other embodiments, the compositions are absorbed,eliminated, or degraded in about 12 hours, 24 hours, or 48 hours.

In certain embodiments, after implantation in vivo, the inventivecompositions absorb and/or disperse from the implant site in less than 7days, preferably less than 4 days and many compositions willsubstantially absorb in less than 192, 120, 96, 72, 48 or 24 hours. Themost preferred compositions will be effective at maintainingintraoperative hemostasis without the need for reapplication for 6 hoursor more and will be substantially resorbed or dispersed within 96 hoursafter implantation.

In some embodiments, particulate solids are included to provide orenhance specific performance characteristics of the formulations. Addedparticles may be absorbable, non-absorbable, or resorbable, or mixturesof particles with a variety of properties may be included according toneed. Particles may be introduced to affect overall dispersion, orelimination of the formulation from the implant site followingimplantation. Particles may be added to affect the handling, stiffness,flowability, osteoconductivity, or water resistance of the formulation.Other examples of additives or fillers or whiskers to provide additionalputty coherence or improve other mechanical properties of thecompositions include poly ether ether ketone (PEEK), REPLACE (Cortek,Inc.), EXPANCEL (Akzo Nobel), natural fibrous materials includingproteins, polysaccharides, extracellular matrix components, absorbablesilks, collagen, fibrin, fibrinogen, thrombin, and absorbable polymersincluding polylactides, polycaprolactones, polyglycolides, polyurethanesand derivatives and combinations or copolymers thereof. In otherembodiments, the particulate material is a ceramic such as substitutedcalcium phosphates (e.g, silica, strontium, or magnesium saltsubstitution) or a glass such as bioglass or absorbable phosphate glass.In some embodiments, the particulate material is one or more of calciumsulfate, calcium phosphosilicate, sodium phosphate, and calciumaluminate. The optional particulate material, when present, may compriseany one or more of the materials listed in the embodiments above.

In certain embodiments, the compositions of the invention do not containadded water. In one embodiment, a composition of the invention isanhydrous.

In one embodiment, the compositions of the invention do not contain anactive chemical hemostatic agent.

In one embodiment, the compositions do not contain dextran, alginate,modified starch, or chitosan.

In one embodiment, the compositions do not contain microfibrillarcollagen.

In one embodiment, the compositions of the invention do not contain ahydrogel forming material such as sodium carboxymethylcellulose.

In one embodiment, the compositions do not contain a thermosettingmaterial.

In certain embodiments, the compositions of the invention do not requirepre-preparation by the application of heat and instead are hand moldableand formable at room temperature.

Preferably, the compositions have a low degree of tackiness and arecompatible with surgical gloves. That is, the compositions do not adhereappreciably to latex or nitrile surgical gloves or similar materials. Atthe same time, the compositions of the invention have sufficient tackstrength to adhere to the moist surfaces of bleeding bone or cartilage.

The compositions are often formed from a process that includes meltingthe combined liquid and solid components into a single homogenous liquidthat is then allowed to solidify. Continuous mixing may be appliedduring the cooling phase to prevent phase separation, when appropriate.Prior to full cooling, the formulations may be introduced into a mold oran extrusion apparatus and may be molded into specific shapes orextruded before or after cooling, depending upon the temperaturedependence of the viscosity of the specific formulation.

FWS-Based Compositions

The compositions of the invention may employ more slowly dissolving FWSnon-particulate bases than described in the art, or otherwise utilize adissolution retardant to slow the dissolution rate. In general, at leastabout 50% by weight of the (particle-free portion) composition is theFWS base. Suitable FWS base materials include moderately hydrophobicmaterials which absorb more slowly than existing formulations (e.g.,than Ostene), may be prepared from moderately hydrophobic solid wax-likematerials such as surfactants with HLB values of less than 20, or lessthan 17, or HLB values of 15 or less. Such surfactants are availablecommercially, for example under the trade names BRIJ, MYRJ, AMITER,CREMOPHOR, and LIPOSORB.

Other FWS base materials include polyethylene glycols of 4,000 kDmolecular weight. and higher. Compositions of the present inventioncomprising such PEG base materials have a 5 to 30-fold dissolution timesthan that a reference. composition (see FIG. 1).

Chemically, suitable FWS base materials include any soluble waxes suchas biocompatible poly(oxiranes) (or poly(alkylene oxides)), block and/orrandom polymers or copolymers of ethylene and propylene glycol andpolypropylene glycol, and their fatty acid ester or ether derivatives.Exemplary polyoxiranes include polyoxirane alcohols, polyoxirane esters(mono, di and poly), polyoxirane ethers (mon, di and poly) andpolyoxirane alkanes. Further non limiting examples of suitable FWS basematerials include water soluble surfactants having HLB values greaterthan 3, 5 or 7, and preferably greater than 10 or 15, but the mostuseful base materials have HLBs less than 20. Non-limiting examplesinclude soluble ethoxylated fatty acids including fatty acid substitutedpolyethylene glycols (PEGs) such as PEG stearate ester, e.g., POLYOXYL40 Stearate (Myrj® 52 (40) Monostearate,), polyethylene glycols (PEGs),substituted PEGS, polyethylene glycol laurate, clerivatized blockcopolymers based on ethylene oxide and propylene oxide (e.g., poloxamersor PLURONICs), soluble sorbitan derivatives, and phospholipids.

For those non-particulate FWS solid bases for which dissolution occursmore rapidly (e.g., low molecular weight surfactants with HLBs greaterthan 15 or 20) than desired, dissolution retardants may be employed. Atypical class of dissolution retardant is the rapidly hydratingpolysaccharides. Sodium carboxymethyl cellulose (CMC) is a member ofthis class. Incorporation (by mixing) of 23% dry CMC powder by weightinto a commercially available product, Ostene, increased its dissolutiontime in the beaker assay by over four fold (see Example 1a & b).Similarly, incorporation of 9.1% CMC into a PEG-based referencecomposition (PEG1450/400—see formula 2a) increased dissolution timeapproximately 15-fold. Additional examples of dissolution retardationafter the incorporation of CMC are provided in examples 1, 2, 3, 5, 11,and FIG. 3.

The dissolution retardant is present at less than about 50% by weight ofthe composition. A retardant (e.g. a liquid surfactant) suitable for usewith a particular base is one that forms a homogenous mixture with thebase and does not phase separate. Hydrogel-forming retardants aregenerally an exception to this principle and are usually included in theformulations in a dry powder form suspended within the formulation.Preferably, the retardant dissolves more slowly than the FWS base. Inone embodiment, the retardant is a rapidly hydrating hydrogel formingmaterial. Suitable gel forming materials include, for example,gel-forming poloxamers (including thermosetting and phase transitioningpoloxamers), hydroxypropylmethylcellulose, chitosan hydrochloride,sodium carboxymethylcellulose, sodium polyacrylic acid, and sodiumpolymethacrylic acid, and polysaccharide glycolates such as the starchglycolates including the sodium salt. When hydrogel-forming materialsare incorporated as the dissolution retardant, gel formation shouldoccur rapidly, i.e., the molecules must readily undergo hydration andgelation prior to full solubilization of the primary component. Duringthe first hour of dissolution, it is preferred that the rate of massloss of the FWS components (as opposed to the hydrogel) relative to thestarting weight of the dry formulation, does not exceed the rate ofwater uptake by the overall formulation (relative to formulationstarting weight). In general, the water uptake rate over the first houris from 75% to greater than 200% of the dissolution rate (measured dry)of the soluble components. In preferred embodiments, water uptake rateis 100%, 125%, 150%, or greater than the dissolution rate. The rate ofwater uptake during the first half hour should also exceed thedissolution rate.

Slow-to-hydrate molecules generally do not form gels prior tosignificant diffusion of the soluble material and therefore cannotimpact the overall dissolution rate of the formulation. Examples ofmaterials that hydrate at an inadequate rate include: sodium alginate,collagen, gelatin, and oxidized cellulose. Hydration inducing mechanismssuch as reduction of particle size and partially pre-hydratedgel-forming materials, and/or pretreatment of the gel forming particleswith a surfactant may be employed to encourage early hydration in theseand similar molecules. Examples of materials which hydrate over asufficiently rapid time course to effectively modulate dissolution ofthe primary soluble component include: substituted polysaccharides,sodium carboxymethylcellulose (low, medium and high viscosities, e.g.,from Sigma Life Sciences), starch glycolates, and chitosanhydrochloride.

For in vitro screening of dissolution properties under the conditionsdescribed herein, a suitable time for complete dissolution in a bufferat 37° centigrade is at least 60 minutes, or from 60 to 90 minutes, 70to 100 minutes, from 90 minutes to 120 minutes, from 2 to 4 hours, from4 to 6 hours, or from 6 to 8 hours. Dissolution time may also beexpressed relative to the “PEG reference formulation” (PEG 1450/400; seeformula 2a). This allows direct comparison of dissolution ratesindependent of the in vitro dissolution method in use. Preferredcompositions will require at least 2.5-fold more time for completedissolution than the PEG reference formulation. More preferably, theinventive compositions will require 3-fold, 5-fold, or greater than10-fold the amount of time required for complete dissolution compared tothe PEG reference formulation. Many embodiments require 12 to 15-fold ormore time to dissolve in the in vitro assay compared to the PEGreference formulation.

Those inventive compositions which comprise sufficiently rapidlyhydrating materials may, upon exposure to an electrically conductiveaqueous medium (e.g., saline or bodily fluids), be able to conduct anelectric charge. Consequently, such formulations, when placed in vivoand exposed to the current produced by electrocautery, in some cases maybe prone to sparking or ignition. The inventors have found that limitingthe dry hydrogel forming material to less than 20% of the totalformulation rate largely eliminates this effect. In order to minimizethis possibility, the preferred compositions will generally contain lessthan about 35%, 30%, 20% or less than 15% of a rapidly hydratinghydrogel forming material. In one preferred embodiment, the formulationcomprises from 25-99% of a non-particulate FWS solid base with an HLB ofless than 20 and 0.5-15% of a dry, particulate rapidly hydratingpolysaccharide (e.g., carboxymethyl cellulose) and is not susceptible toignition or sparking within the composition when exposed toelectrocautery in the presence of saline solution.

Further non-limiting examples of suitable dissolution retardants includepoorly water soluble liquids, chemical binders, emollients, detergentbuilders, and suspending agents. Suitable poorly water soluble liquidsinclude liquid PLURONICs (block copolymers based on ethylene oxide andpropylene oxide, also referred to generically as “poloxamers”) having anHLB less than 10, liquid glycerol fatty acid esters (e.g., glycerol monocaprylate, and glycerol monocaprate), isocetyl alcohol, Eastman SAIB,and liquid tocopherols including tocopherol acetate. Polypropylene oxideis an insoluble alkylene, oxide polymer that has been found toadvantageously reduce dissolution and promote water resistance of someof the inventive compositions utilizing alkylene oxide-based polymers asthe FWS, non-particulate base. Non-limiting examples of suitable bindersinclude cellulose esters and hydrogel forming polymers such ashydroxylethyl cellulose, carboxymethyl cellulose (e.g., sodium,potassium, and lithium salts; commercially available FINNEIX from CPKelco), hydroxypropylmethylcellulose hypromellose, USP), and sodiumalginate. Non-limiting examples of emollients include octyl palmitate,microcrystalline cellulose (AVICEL PH). Non-limiting examples ofdetergent builders include low molecular weight polyacrylic acids,sodium polyacrylate, and salts of poly aspartic acid and poly glutamicacids. Non-limiting examples of suspending agents include sodiumpolyacrylic acid (CARBOPOL).

In certain embodiments, the FWS-base comprises at least 50 wt % of thenon-particulate portion of the composition with the remaining weightcomprising one or more dissolution retardants and one or more optionalparticulates. In one embodiment, the one or more particulates is anosteoconductive material selected from bone or a bone substitute,calcium phosphate; tricalcium phosphate (e.g., alpha or beta tricalciumphosphate), tetracalcium phosphate; dicalcium phosphate; poorlycrystalline hydroxyapatite, substituted calcium phosphates (e.g., withmagnesium, strontium, or silica salts): calcium pyrophosphate,hydroxyapatite, biphasic calcium phosphates, hydroxyapatite and TCPcontaining calcium phosphates, multiphasic calcium phosphates, andglasses—both silicate and phosphate based, highly porous nanocrystallinehydroxyapatite (HA) in the presence of nanoporous silica (SiO₂) in asol-gel combination; glass-ionomer, absorbable phosphate glass, calciumsulfate, an osteoconductive plastic (e.g. tyrosine polycarbonates ortyrosine polyarylates and derivatives), polymer or polyurethane, or anycombination thereof.

In one embodiment, the composition comprises an osteoconductive materialin particulate form in an amount of from about 5 to 70% (wt/wt), 5 to50%, 20 to 30%, or 1 to 20% of the final composition. In one embodiment,the one or more osteoconductive materials are in the form of a particle,a fiber, or a whisker with minimal cross-sectional diameters rangingfrom 0.00001-100 mm. In a preferred embodiment the average particlediameter is between 100 to 750 microns. In a more preferred embodimentthe particles are rounded and microporous. In another embodiment, theparticulate ceramic comprises less than 75%, less than 50%, less than40%, 35%, less than 30% or less than 20% of the total volume of thecomposition.

In one preferred embodiment of the invention the formulation comprisesparticles embedded within a putty-like soft, solid wax (e.g., asurfactant) base. The presence of the particles provides a.) frictionalresistance to facilitate purchase of the formulation of the puttyagainst the surface of bone, and improve retention of the putty at theimplant site, b.) improved handling and putty stiffness, and optionally,c.) radiopacity to the formulation. In more preferred aspects of thisembodiment, the particles are rounded or spherical to further optimizemoldability and spreadability at the implant site (compared to irregularparticles which create resistance to moldability and spreadability)while still improving frictional resistance compared to the absence ofparticles. In still more preferred embodiments, the rounded particlescomprise a microporous ceramic (e.g., glass, bioglass, calcium phosphateand/or calcium carbonate, and their derivatives), having average poresize of less than 1000 microns, less than 75, 50, 25,10, 5 or less thanone micron. In other preferred embodiments, the rounded microporousparticles comprise a biphasic calcium phosphate (e.g. HA/TCP with weight% ratio of hydroxyapatite of 5, 15, 25, 40, 50 or 60%) and have adensity of 0.7, 1, 1.5, 2, 2.5, 3, or greater than 3 gm/cc. Finally, theinvention contemplates a bone void filler with or without hemostaticproperties (e.g. a hemostatic bone substitute) comprising anon-particulate water soluble surfactant with an HLB of less than 20(eg, polyoxyethylene 40 stearate) and further comprising roundedmicroporous ceramic particles of 15-55% by weight, where in theparticles have a bulk density greater than 2.5 gm/cc.

PWS-Based Compositions

The compositions of the invention having a non-particulate PWS baserequire a dispersion accelerant that may be non-particulate orparticulate. As used herein “non-particulate PWS base” means the PWSmaterial is either sourced as a monolithic wax or was prepared from amelt of a particulate base. In certain embodiments, the composition isformed from one or more PWS bases and/or one or more accelerants.

In accordance with this embodiment, at least about 50% by weight ofcomposition is the PWS base. Suitable PWS base materials include mono-,di-, or tri-fatty acid esters such as glycerol and sorbitan mono fattyacid esters (stearates, palmitates, laurates), and cholesterols. Othersuitable insoluble and poorly soluble waxes are known to the art and arecataloged in McCutheon's (2009) (volumes 1 & 2 ManufacturingConfectioner Publishing Co. Princeton, Wis.).

The dispersion accelerant is present at less than 50% by weight of thecomposition. Preferably, the accelerant is present in an amount that isabout 1.0 to 20% or 1 to 10% by weight of the composition. A suitableaccelerant for use with a particular base is one that forms a homogenousmixture with the base. Accelerants generally serve to disperse orsolubilize the base within an aqueous environment. When an insolublestearate wax is used, preferred accelerants include soluble stearatessuch as PEG stearate, liquid glycerol fatty acid monoesters, low HLBliquid surfactants (e.g., <20).

In one embodiment, particles are used to promote the aqueous dispersionof the PWS base. In accordance with this embodiment, the particles aregenerally hydrophilic, poorly soluble in water, and metabolizable (e.g.,biocompatible ceramics, calcium phosphate, hydroxyapatite, tricalciumphosphate, bioglass, demineralized bone, mineralized cancellous orcortical bone, lyophilized protein, allograft, xenograft, and/orautogenous bone). In some cases the particles are freely soluble inwater soluble, biocompatible salts of calcium phosphate, sugars, salts,polysaccharides, hydrogels formers and/or precursors, etc.). Particulatedispersants may be in granular or powder form, micron or submicron insize. In this context, the size refers to the size of the particle inits largest dimension and is generally given as a mean average particlesize. Preferably, the particles are 1000 microns or less in size. Incertain embodiments the particles are 750 microns or less, 500 micronsor less, 250 microns or less, or 100 microns or less in size. Whensubmicron particles are used as accelerants, their particle size canrange from 0.1 to 1, 5, 10, or 50 microns.

In other embodiments, hydrotropic coupling agents are preferredaccelerants. These include glyceryl caprate or caprylate (Capmul,Captex, etc) or organic phosphate derivatives such as lecithin andwater-based organofunctional silanes. Some preferred accelerants have anaffinity for the PWS (e.g., PEG stearate and glycerol monostearate).

In certain embodiments, the PWS-based composition comprises at leastabout 50% of the PWS base, one or more dispersion accelerants and one ormore particulates. In one embodiment, the one or more particulates is anosteoconductive material selected from the same list of materialspreviously described for FWS formulations. In one embodiment, thecomposition comprises an osteoconductive material in an amount of frontabout 5 to 50% (wt/wt), 5 to 40%, 20 to 30%, or 1 to 20% of the finalcomposition. In one embodiment, the one or more osteoconductivematerials are in the form of a particle, a fiber, or a whisker withminimal cross-sectional diameters ranging from 0.00001-1.00 mm.Considerations for included particulates in the PWS formulations are thesame as with FWS compositions.

Therapeutic Agents

The compositions of the invention may optionally include one or moretherapeutic agents. In various embodiments, the therapeutic agents areadded to the compositions of the invention in solid form, eitherdirectly to the melted mixture of components when the therapeutic agentis heat stable, or during or after solidification by mixing or blending.The one or more therapeutic agents may be any suitable or desirabletherapeutic agent known to the skilled artisan. In a specificembodiment, a composition of the invention optionally comprises one ormore of an antimicrobial, a local anesthetic or analgesic, ananti-inflammatory agent, a bone growth stimulating agent, a radiopaqueagent, or an antioxidant.

In one embodiment, the compositions of the invention comprise one ormore antimicrobial or antibiotics. Non-limiting examples of suitableantibiotics include broad spectrum antibiotics (e.g., gentamicin,clindamycin, crythromycin), gram-positive and gram-negative families ofantibiotics (e.g., ampicillins and cephalosporins). In one embodiment,the composition also comprises agents such as TRICLOSAN, chlorohexidine,iodine, povidone iodine, colloidal silver, etc.

In one embodiment, the compositions of the invention comprise one ormore local anesthetics or analgesics. Non-limiting examples includelidocaine, bupivacaine, tetracaine, and ropivacaine. Further examplesinclude benzocaine and fentanyl (a potent non-opioid).

In one embodiment, the compositions of the invention comprise one ormore anti-inflammatory agents such as non-specific ibuprofen andaspirin, or COX-2 specific inhibitors such as rofecoxib and celeboxib.

In one embodiment, the compositions of the invention comprise one ormore antioxidants. Non-limiting examples of suitable antioxidantsinclude IRGANOX 1010 and IRGANOX 1035 (Ciba Geigy), CYANOX 1790 andCYANOX 2777 (Cytec Industries), and vitamin F and vitamin E acetate(BASF Corp.). In certain embodiments, the antioxidant is present in anamount of from about 0.01% to 0.5% by weight of the composition.

In one embodiment, the compositions of the invention comprise one ormore bone growth stimulating or osteoinductive agents such as peptidegrowth factors, bone morphogenetic proteins (BMP, e.g., rhBMP-2);demineralized bone matrix; transforming growth factors (TGF, e.g.,TGF-(3); osteoblast cells, growth and differentiation factor (GDF), andcombinations thereof. Further examples include other hone stimulatoryorganic agents including HMG-CoA reductase inhibitors, such as a memberof the statin family, e.g., lovastatin, simvastatin, pravastatin,fluvastatin, atorvastatin, cerivastatin, mevastatin, andpharmaceutically acceptable salts, esters or lactones thereof.Additional embodiments include pyrrolidones, prostaglandins, vitamins,bis phosphonates, phospholipids and combinations of any of theforegoing.

Other Optional Components

The compositions of the invention may also comprise one or more optionalcomponent including, without limitation, those described herein. In oneembodiment, a composition of the invention comprises one or more activeagents. In one embodiment, the one or more active agent is selected froman antimicrobial agent, an anesthetic, an analgesic, ananti-inflammatory agent, an osteoconductive agent, and achemotherapeutic agent. In one embodiment, a composition of theinvention further comprises one or more of a softening agent, achelating or sequestering agent (e.g., sodium gluconate, polyasparticacid, and EDTA), and a filler or thickener. In one embodiment, acomposition of the invention further comprises one or more of aradiotransparent agent, a radiopaque agent, an antioxidant, ananti-adhesion agent (e.g., hyaluronic acid), and a colorant (e.g.,gentian violet, D&C Violet #2, and D&C Green #6). In certainembodiments, a composition of the invention may comprise a combinationof arty of the foregoing.

Non-limiting examples of suitable antibiotics include broad spectrumantibiotics (e.g., gentamicin, clindamycin, erythromycin), gram-positiveand gram-negative families of antibiotics (e.g., ampicillins andcephalosporins).

Non-limiting examples of suitable anesthetics or analgesics includelidocaine, bupivacaine, tetracaine, and ropivacaine. Further examplesinclude benzocaine and fentanyl (a potent non-opioid).

Non-limiting examples of suitable anti-inflammatory substances includethe non-specific drugs, ibuprofen and aspirin or the COX-2 specificinhibitors such as rofecoxib and celeboxib.

Non-limiting, examples of suitable osteoconductive agents for use asadditives in the compositions of the invention include, for example,collagen, a calcium phosphate (such as hydroxyapatite, tricalciumphosphate, or fluorapatite), demineralized bone matrix, and combinationsthereof.

Non-limiting examples of suitable antioxidants include IRGANOX 1010 andIRGANOX 1035 (Ciba Geigy), and CYANOX 1790 and CYANOX 2777 (CytecIndustries). In certain embodiments, the antioxidant is present in anamount of from about 0.01% to 0.5% by weight of the composition.

An additional softening component is sometimes required in order to makethe monolithic solid more pliable. This is particularly required forcompositions employing Poloxamers with molecular weights in excess of500 kD (e.g., Pluronic F-127) and polyethyleneglycol based materialswith molecular weights greater than 4000 kD. In preferred embodiments,the dispersion accelerant also serves as a softener. In any case,suitable softeners are often insoluble or low solubility liquid or pasteemollients or surfactants (e.g., Pluronic L-123). Many preferredsofteners arc insoluble or low solubility neutral surfactants with HLBsless than 40, preferably less than 30, more preferably less than 20.Most preferable surfactants for this use have HLBs less than 10 andinclude Pluronic L-121, L101, and L-123. Eastman SAIB, tocopherol andits derivatives may also be useful as softeners.

Optional fillers and thickeners for use as additives in the compositionsof the invention include, for example, cholesterol, calcium carbonate,starch, modified starch, starch derivatives, mineral and vegetable oils(e.g., castor bean oil, sunflower oil, olive oil, and purifiedderivatives thereof), glycerol and glycerol derivatives, microcrystalline cellulose, gums, sorbitans and sorbitol derivatives.

Non-limiting examples of a radiotransparent substance include air,nitrogen gas, carbon dioxide, and oxygen gas. Non-limiting examples of aradiopaque substance include barium sulfate (BaSO₄), ceramic particles,bone, and zirconium dioxide (ZrO2). Examples of commercially availableradiopaque substances include LIPIODOL, HYPAQUE, and OMNIPAQUE. At leastone radiotransparent substance and/or radiopaque substance, whenpresent, is present in the compositions in an amount of from about 0.1%to about 40% by weight of the composition, and, in embodiments, fromabout 0.1% to about 10% by weight of the composition.

Dissolution Assays

The compositions of the invention have enhanced durability in thesurgical environment in part due to their decreased water solubility.The dissolution time of compositions is tested, for example, in an invitro assay. In one such assay, the test composition is formed into adisk of uniform dimension and placed in a 37° C. water bath. The time todissolution or dispersion is measured.

Beaker Dissolution Screening Method

In the results reported here for the Beaker dissolution screeningmethod, samples were manually formed into a uniform disc, 14 mm wide and3 mm thick. The discs were submerged into dissolution buffer by pressingthem onto the side of a glass beaker containing 200 ml of phosphatebuffer, pH 7.4, at 37° C. below the buffer surface. The submerged discswere observed every thirty minutes or until complete dissolutionoccurred and the time of dissolution was recorded.

Biopsy Bag Dissolution Screening Method

In a variant of the dissolution assay, the test composition is formedinto a disk of uniform dimensions and its weight is recorded. The weightof a corresponding number of biopsy bags is also recorded. Disks areplaced into biopsy bags, fitted with a weight and submerged into abuffered dissolution bath. At specific time points the submerged discsare retrieved, dried, and weighed to determine the weight of theformulation lost to dissolution.

In the examples reported herein, an equal amount of each sample wasmanually pressed into a uniform disc (14 mm wide and 3 mm thick), andplaced into a biopsy bag (45×75 mm, 200 mesh, VWR catalog #29000-050)and briefly clipped into a potassium phosphate buffer solution (50 mM).The bag containing each sample was then blotted for 4 seconds and itsweight recorded. The bags were secured with a dialysis bag closuredevice and placed into a potassium phosphate buffer solution bath atsecured inside a biopsy bag and placed into a glass beaker containing˜400 ml of phosphate buffer, pH 7.4, at 37° C.

At the indicated time points, samples were removed from the bath and thedialysis closure released. The sample is blotted for 4 seconds and thenweighed and the percentage of the sample remaining was calculated.

Wire Mesh Dissolution Screening Method

Another in vitro variant of the dissolution assay for which results arereported herein replaces the biopsy bag with a mesh cup for holding thetest article. An equal amount of each sample was compacted into 60-mesh(250 micron) baskets (McMaster Carr Part #14416 FW 0.600), placed intobeakers containing ˜400 ml phosphate buffered saline, and maintained at37° C. and agitated at ˜20-25 rpm shaker speed. At the indicted timepoints the basket was removed from the bath, weighed wet, and air driedovernight and weighed again to determine dry weight. Dry weights areused to determine dissolution rates, and wet weights are used todetermine the rate of water uptake.

In Vitro Hemostasis Model

The relative hemostatic efficacy of the compositions of the inventioncan be evaluated in vitro, for example, by the HEM test or a similartest. The HEM test evaluates both adherence to bone or similar materialand solubility in the presence of water. If adherence is too weak or ifthe composition is too water-soluble, it will not provide an acceptabletamponade hemostasis. The HEM test mimics one of the most demandingsituations for tamponade hemostasis in orthopedic practice—the pediclescrew hole. A pedicle screw hole is a hole drilled into spinal bone bythe surgeon. It is often as large as 6 mm in diameter. In the context ofthe HEM test, the pedicle screw hole is mimicked by drilling a 6 mm hole(in some variations other diameter holes are employed which may be 2, 3,4, or 5 mm) into a full-thickness section of central bovine tibia. Aclosed system is created by sealing the ends of the bone section with aresin. The resin accommodates tubing that shunts water into and out ofthe center of the bone. (i.e., where the marrow would be in theintramedullary canal). The composition to be tested is uniformly packedinto the 6 mm hole and subjected to the shear force of water flowingthrough the center of the bone. The amount of time for which thecomposition is able to withstand the flow is measured, to a maximum timeof 3600 seconds.

The compositions of the invention can also be evaluated for tamponadeefficacy in vivo, for example, by its ability to produce hemostasis inliving rabbit bone. In this test, a 4 mm hole is drilled through thecortices of the humerus into the intramedullary canal. Once activebleeding is confirmed, the test compound is applied to the defect. Eachcompound is applied at 4 or 5 different sites in different animals.Hemostasis is monitored in two ways. First, the time to hemostasispost-application is recorded. This is measured from the time of removalof excess material to the cessation of bleeding. Second, hemostasisefficacy is measured by recording whether or not hemostasis ismaintained without significant re-bleeding or leakage for the durationof the experiment. In addition, the handling properties of eachcomposition are evaluated by the surgeon. The surgical testers are askedto estimate the preparation time which includes any kneading, warming,or mixing time required prior to application. The testers are also askedto judge the ease of application as poor, fair, good, or excellent andto comment on the handling properties of the putty (pliability,stickiness). Preferably, the compositions of the invention stop theactive bleeding within a few seconds or at least within 1 minute afterapplication to the site and maintain hemostasis for at least 1 to 3hours.

In certain embodiments, the hemostasis efficacy of the compositions ismeasured with an in vitro assay such as the HEM test described herein.Preferably, the compositions of the invention are able to maintainhemostasis in such an assay for at least 30 minutes at least 90 minutes,at least 12.0 minutes, or for from about, 30 to 60 minutes or 120minutes, 90 to 120 minutes, 120 to 180 minutes, 180 to 240 minutes, orlonger.

Tactile Proper

The compositions of the invention also have specific tactile properties.For example, the compositions of the invention have a suitablestiffness, spreadability, stickiness, and slipperiness. Stiffness is ameasure of how rigid or fluid the composition is when manipulated byhand. This is important because for effective application to bleedingbone surfaces, the composition cannot be too rigid or too fluid.Preferably, the compositions of the invention have a “putty-like”consistency. This quality is evaluated by manually manipulating thesample with surgical gloved hands. Spreadability is a measure of howeasily and uniformly the composition spreads over a bone surface so thatall pores are evenly blocked. This is evaluated by spreading a 1 cmdiameter sphere of the composition across a simulated bone (Sawbone) andmeasuring, in centimeters, the length of the track produced. Stickinessis a measure of cohesiveness on surgical gloved hands. This is evaluatedby pressing a 1 cm diameter sphere of the composition between two glovedfingers and estimating the quantity of material sticking to the opposingfinger. Slipperiness may also be evaluated using a similar test with theexception that the sphere is first submerged in a 37° C. water bath andthen handled. All of these properties affect the ability of thecomposition to be used easily and effectively during surgery. Theseproperties are preferably measured by a panel of from 4 to 10 evaluatorswho grade each of the three properties on a scale of 0 (best) to 5(worst). Exemplary scales for each of the three properties are given inTable 1.

TABLE 1 Spreadability Stickiness Grade Stiffness (on model bone) (tolatex gloves) 0 Putty Excellent - Softest No Adhesion 1 Paste Good -Soft Slight 2 Wax Substantial Moderate 3 Gel Moderate Substantial 4Solid or Powder Hard Severe 5 Fluid Hardest Bonding to glove surface

In many cases the slower solubilization tine of the inventive puttiesleads to reduced slipperiness compared to a reference composition.Reduced slipperiness in aqueous environments offers improved surgicalusefulness in handling and placement of the hemostatic putties.Slipperiness can also be reduced through incorporation of many of thedescribed granular materials (e.g., particulate ceramics and glasses).In one embodiment, a composition of the invention has reducedslipperiness compared to a reference composition selected from OSTENE; acomposition exemplified in U.S. Pat. Nos. U.S. Pat. No. 7,553,913 andU.S. Pat. No. 7,829,616 by Wellisz, et al., and a compositionexemplified in U.S. Pat. No. 7,074,425 by Constantine, et al. Inpreferred embodiments, the slipperiness of a composition of theinvention after exposure to water is at least 10% less than a referencecomposition.

Slipperiness can be determined empirically through the measurement ofthe coefficient of friction. Guidance for measurement of the coefficientof friction can be found in ASTM C 1028-07. A useful instrument ofquantification is the pull-meter, commercially available from GabrielliTechnology (code GT0810 or GT0966). Preferably, the coefficient offriction is determined in both the wet and dry conditions using theGabbrielli Pull-meter according to ASTM C 1028-07. In one embodiment, acomposition of the invention has an increased coefficient of frictioncompared to a reference composition selected from OSTENE; a compositionexemplified in U.S. Pat. Nos. U.S. Pat. No. 7,553,913 and U.S. Pat. No.7,829,616 by Wellisz, et al., and a composition exemplified in U.S. Pat.No. 7,074,425 by Constantine, et al. In one embodiment, the coefficientof friction for a composition of the invention is at least about 10%higher than that of the, reference composition.

The compositions of the invention have the consistency of a putty.Compositions having a suitable putty-like consistency are characterizedby their stiffness or viscosity. In certain embodiments, thecompositions of the invention have an improved stiffness compared toreference composition. In certain embodiments, the reference compositionis selected from commercial bone hemostats such as BONE WAX, OSTENE, andHEMASORB. In other embodiments, the reference composition is selectedfrom a composition exemplified in U.S. Pat. Nos. 7,553,913 and 7,829,616by Wellisz, et al., and a composition exemplified in U.S. Pat. No.7,074,425 by Constantine, et al. In one embodiment, a composition of theinvention is less stiff than a reference composition selected from BONEWAX and OSTENE, a composition exemplified in U.S. Pat. Nos. 7,553,913and 7,829,616 by Wellisz, et al., and a composition exemplified in U.S.Pat. No. 7,074,425 by Constantine, et al. In one embodiment, acomposition of the invention has about the same stiffness as a referencecomposition selected from HEMASORB.

The relative stiffness or viscosity of a composition can be measuredusing techniques known in the art. In one example, stiffness is measuredusing a hand penetrometer. The putty is placed in a 13 by 3 mmcylindrical sample holder and a spatula is used to level and smooth thesurface of the sample. The sample is maintained in the block for 1minute at room temperature. A hard wax is prepared by removing frompackaging and placing on a flat surface without pre-handling under thepenetrometer tip. Samples are tested on a calibrated penetrometer with a50 gram weight. Specifically, the 50 gram weight is placed on top of theplunger rod (the hole in the center of the weight centers the weight onthe plunger rod) and the top and lower locking screws are loosened tolower the head of the penetrometer so that the tip of the cone justtouches the surface of the sample. The penetrometer head is then securedin place with the locking screws. At time zero, the plunger is releasedand held for 5 seconds to lock it in place at the depth of penetration.The indicator rod is pushed so that it comes into contact with the topof the plunger. Other standard methods may be employed including, e.g.,parallel plate viscometers.

EXAMPLES Example 1 FWS Screening

Certain gel-forming additives have been found to be particularlyeffective dissolution retardants in the FWS-based compositions of theinvention. In particular, sodium carboxymethylcellulose of low, mediumand high viscosities such as CMC LV, CMC MV and CMC HV were found tosignificantly increase the dissolution time of the FWS-basedcompositions as assayed in the in vitro test described above. Incontrast, neither chitosan, sodium alginate, gelatin, nor oxidizedcellulose, added in the same proportion as CMC, increased thedissolution time of the composition. This finding is illustrated by thefollowing examples.

Each of the following samples was prepared by melting the listedcomponents while stirring followed by stirring the melt while it cooledto ambient temperature and solidified. When CMC was used in a particularformulation it was added to the melted components as a powder and thecomposition cooled with stirring to form a putty-like material. Allsamples were allowed to sit at least 24 hours at room temperature, priorto screening for dissolution properties by the Beaker Method.

TABLE 2 Dissolution # Formulation Assayed by the Beaker Method time(min) 1a OSTENE 105 1b OSTENE/CMC (MV) - 77%/23% 450 2a PEG 1450/PEG400 - 90%/10% 30 2b (PEG 1450/PEG 400)/CMC (MV) - 450 90.9%(81.8/9.1)/9.1% 2c (PEG 1450/PEG 400)/sodium alginate - 30 90.9%(81.8/9.1)/9.1% 2d (PEG 1450/PEG 400)/chitosan - 30 90.9%(81.8/9.1)/9.1% 2e (PEG 1450/PEG 400)/gelatin - 66% (90/10)/−33% 30 2f(PEG 1450/PEG 400)/oxidized cellulose - 30 90.9% (81.8/9.1)/−9.1% 3a PEGStearate - 80%/PLU L-121 - 20% 30 3b PEG Stearate - 60%/CMC (MV) - 20%/300 PLU L-121 - 20% 3c PEG Stearate - 80%/PLU L-121 - 15%/TOC - 5% 30 3dPEG Stearate - 60%/CMC (MV) - 20%/ 330 PLU L-121 - 15%/TOC - 5% 3e PEGStearate - 40%/CMC (MV) - 40%/ 450 PLU L-121 - 15%/TOC - 5% 4a PLUF-127 - 77%/PLU L-121 - 23% 420 4b PLU F-127/PLU L-121 - 64.5%/ 390 CMC(MV) - 32.3%/TOC - 3.2% 5a PLU F-68 - 77%/PLU L-61 - 23% 60 5b PLUF-68 - 55.6%/PLU L-61 - 11.1%/ 420 CMC (MV) - 33.3% 5c PLU F-68 -67%/PLU L-61 - 23%/CMC (MV) - 10% 210 5d PLU F-68 - 67%/PLU L-61 -23%/CMC (LV) - 10% 180 5e PLU F-68 - 76.92%/PLU L-61 - 18.46%/TOC -4.62% 90 5f PLU F-68 - 38.46%/PLU L-121 - 18.46%/ 430 CMC (MV) -38.46%/TOC - 4.62% 5g PLU F-68/PLU L-121 - 66.67%/CMC (MV) - 33.33% 4205h PLU F-68/PLU L-121 - 66.67%/CMC (LV) - 33.33% 180 5i PLU F-68/PLUL-121 - 66.67%/CMC (HV) - 33.33% Hard, not evaluated 6a PEG Stearate -80%/PLU L-121 - 10%/ 30 Polypropyleneglycol 2000 - 10% 6b PLU P-123 -67%/PLU F-127 - 33% 200 Abbreviations: PLU—Pluronic (BASF), L—LiquidPluronic, F—Solid Pluronic; CMC—sodium carboxymethylcellulose (SigmaAldrich), (HV)—High Viscosity, (MV)—Medium Viscosity, (LV)—LowViscosity; TOC—Tocopheryl Acetate (BASF); PEG—Polyethylene Glycol(Spectrum); PEG Stearate - polyethylene glycol stearate ester, i.e.,Polyoxyl 40 Stearate (Myrj^(R) 52 = Polyethylene Glycol (40)Monostearate, USP, NF) (Spectrum); OSTENE (Ceremed, Inc., Lot #W1570906).

Screening of these formulations revealed the addition of CMC toformulations 1a, 2a, 3a, 5a, 5e resulted in significantly prolonged,dissolution times. It is not known why the addition of CMC has such aremarkable effect on the rate of dissolution of the composition. Withoutbeing hound by any particular theory, one explanation for why theinclusion of CMC retards dissolution is that the hydrogel formed by theaddition of a CMC-containing sample to warm buffer encapsulates theputty components within a CMC hydrogel, retarding dissolution by forcingcomponent diffusion through the surrounding hydrogel or, alternatively,by forming a concentration gradient within the hydrogel that retardsdissolution. An alternative is that dissolution retardation may resultfrom hydrogen bonding between the components and the CMC hydrogel. Yetanother possible explanation is that dissolution retardation resultsfrom a phenomenon analogous to gel partition chromatography wheremolecules diffuse through a hydrogel as a function of their molecularweight. The latter may explain why higher molecular weight Pluronicmixtures, e.g., ˜4000, (Sample 3) do not require CMC to extenddissolution time.

Example 2 FWS Dissolution kinetics

Dissolution curves were determined either using the Biopsy bag or themesh basket approach. The data for the formulations listed in Table 3are presented in FIGS. 1-4. Using the Biopsy hag dissolution method thefollowing formulations were used to generate the data presented in FIGS.2 & 3.

TABLE 3 Extrapolated Time to complete Dissolution Dissolution #Formulations Method (mins)  7a Ostene BB  60  7b PEG reference: PEG1450 - 90%/ BB  10 PEG 400 - 10%  8a PLU F-127 - 60%/PLU L-121 - BB >30030%/HA/TCP - 10%  8b PLU P-123 - 67%/PLU F-127 - 33% BB >300  8c PLUF-127 - 77%/PLU L-121 - 23% BB  180  8d PEG Stearate - 75%/CMC(MV) - 5%/BB  240 PLU L-121 - 10%/ Polypropyleneglycol 2000 - 10%  9a PEG4K -70%/PLU P-123 - 30% BB >300  9b PLU F-127 - 77%/PLU L-121 - 23% BB  180 9c PEG Stearate - 75%/PLU L-121 - BB >100 20%/CMC - 5% 10 PEGStearate - 35%/CMC(MV) - 5%/ MB  360* PLU L-121 - 5%/ TOC - 5%/HA/βTCP -50%

Example 3 FWS Water Uptake and Dissolution The Effect of IncorporatingCMC and Gamma Irradiation (Irradiation Dose)

The effect of CMC on the rate of water uptake in a putty with or withoutexposure to gamma irradiation was evaluated using the followingformulations. Results are presented in Tables 4-6 and in FIG. 3.

TABLE 4 Extrapolated Time to complete Dissolution # Formulation: MeshBasket Method (mins) 11a PEG Stearate - 74%/CMC (HV) - 6%/ 600 PLUL-121 - 10%/Polypropylene glycol 2000 - 10% 11b PEG Stearate - 80%/PLUL-121 - 10%/ 240 Polypropylene glycol 2000 - 10%

TABLE 5 Water Water Uptake Uptake @ Water @ 0.5 hrs 1 hrs Uptake @ 5 hrsWSH (no gamma) 30% 43% 79% WSH (no CMC) 0 0 0 WSH (gamma) 17% 46% 65%

TABLE 6 % Mass % Mass % Mass % Mass loss @ loss @ loss @ loss @ 0.5 hrs1 hrs 3 hrs 5 hrs WSH (no gamma) 18 32 77 WSH (no CMC) 25 75 100* WSH(gamma) 16 32 72 *fully dissolved at 4 hours

The effect of the incorporation of particulate calcium phosphate wasevaluated using the mesh basket method for the formulations in Table 7.Results of the evaluation of the formulations listed in Table 7 arepresented in Table 8.

TABLE 7 Expected Dissolution Time # Formulation (mins) 12a PEGStearate - 75%/CMC - 5%/PLU L-121 - 10%/ 600  Polypropylene glycol2000 - 10% 12b PEG Stearate - 35%/CMC (MV) - 5%/PLU L-121 - 360*5%/TOC - 5%/HA/β-TCP - 50% */HA/β-TCP component will persist for weeks

TABLE 8 mean % water up mean % take mass loss hrs X (SD) X (SD) 1 31.4(1.2) 19.2 (1.5) 3 50.0 (3.7) 38.4 (3.5) 6 61.8 (1.6) 62.2 (2.9)

Example 4

Use of high molecular weight polyethylene glycols to produce longerdissolution time putties. These PEGS are provided has hard waxy powders.To produce a putty they were melted in the presence of Pluronic P123, aVaseline-like wax. The melt was cooled with continuous mixing to producea formable putty. Dissolution rates were determined after 24 hours. Eachof these materials underwent complete dissolution over a time period 5to 40 times longer than the reference materials (FIG. 1 A-B). Theresults are presented in Table 9.

TABLE 9 Time to Complete Dissolution # Formulation (min) 13a Peg 4k -70%/PLU P-123 - 30% 300 13b Peg 6k - 70%/PLU P-123 - 30% 400 13c Peg8k - 70%/PLU P-123 - 30% 400 13d Peg 10k - 70%/PLU P-123 - 30% 400

Example 5 PWS-Based

Compositions were prepared as described ie and tested for dispersaltime, since these materials do not completely dissolve. Since thesesamples were prepared from less soluble components, dispersion wasevaluated every 24 hours. The formulations listed in Table 10 weretested.

TABLE 10 Observations after 24 hr at 37 C. Sample Components Beaker testHandling 14 62.5% SMS/27.5% L-121/10% F-68 intact good 15 52.5%SMS/27.5% L-121/20% F-68 intact good 16 42.5% SMS/27.5% L-121/30% F-68partially good disintegrated 17 32.5% SMS/27.5% L-121/40% F-68 partiallygood disintegrated 18 40% CS/20% TCPμm/35% L-121/5% intact good TA 1942.5% GMS/27.5% L-121/30% F-68 partially good disintegrated 20 67.5%SMS/27.5% L-121/5% P-123 intact good Abbreviations: SMS—SorbitanMonostearate; L-121—Pluronic L-121; F-68—Pluronic F-68; TCPμm—TricalciumPhosphate (micronized); CS—Calcium Stearate; TA—Tocopheryl Acetate;GMS—Glycerol Monostearate.

These data indicate that formulations 16, 17 & 19 disperse well and areexpected to clear well in vivo.

Additional formulations were prepared, which are listed in Table 11.

TABLE 11 Beaker test minutes 21 CHOL - 55%/PLU P-123 - 45% 200

Other Formulations

Other useful formulations for the preparation of PWS hemostaticcompositions are listed in Table 12.

TABLE 12 # Components Comment 22 60% SMS/40% L-121 Forms well, somewhatsticky 23 70% SMS/30% L-121 Forms well, somewhat sticky after coolingand handling 24 75% SMS/25% L-121 Crumbly after cooling 25 67.5%SMS/32.5% L-121 Very good formation/handling; some SMS reformed aftercooling 26 67.5% SMS/27.5% L-121/ Forms, handles well 5% P-123 27 60%GMS/30% L-35/10% TA Forms well, but sticky 28 67.5% GMS/22.5% L-35/Slightly gritty/sticky 10% TA 29 50% GMS/30% L-121/20% Good handling andforms well; PEG 1500 becomes tacky after continued manipulation 30 50%GMS/30% L-121/20% No stickiness after prolonged PEG 2000 manipulation;does become a ‘rock’ after sitting out 31 45% GMS/45% IPM/10% Goodputties dispersed after 24 hrs @ PEG-stearate 37 degrees 32 40% GMS/20%IPM/20% Good putties dispersed after 24 hrs @ PEG stearate20% PLU 121 37degrees 33 60% PEG 1500/20% L-121/ Forms and handles well; leaves a 20%GMS little residue after prolonged manipulation 34 42.5% Bonewax/27.5%L-121/30% F-68 35 42.5% Bonewax/27.5% GMC/30% F-68 36 42.5% GMS/27.5%glycerol mono caprylate/30% F-68 37 30% hypromellose/42.5% SMS/27.5%L-121 Abbreviations: SMS—sorbitan monostearate; L-121—Pluronic L-121;F-68—Pluronic F-68; TCPμm—tricalcium phosphate (micronized); CS—calciumstearate; TA—tocopheryl acetate; GMS—glycerol monostearate; GMC—glycerolmono caprylate.

Example 6 In vivo HEMOSTASIS

Various formulations were tested for their hemostatic efficacy insurgically created defects in the distal femur of New Zealand White(NZW) rabbits. 4 mm diameter holes were drilled in surgically exposedlateral and medial cortices of the epicondyles. Active bleeding wasconfirmed at each defect site prior to the application of the hemostaticmaterials. The test articles were then kneaded to the desiredconsistency if necessary, and applied to the bleeding defect toestablish hemostasis. In all examples hemostasis was achievedimmediately upon placement of the putty.

TABLE 13 Range of Hemostasis Time (in-vivo) Formulations for in vivohemostasis (mins) FWS Formulations 38a PEG Stearate - 75%/CMC (MV) - 5%/<5 PLU L-121 - 15%/TOC - 5% 38b PEG4K - 70%/PLU P-123 - 30% <15 38c PEGStearate - 75%/PLU L-121 - 20%/CMC - 5% <15 38d PEG Stearate - 75%/CMC -5%/PLU L-121 - 10%/ >15 Polypropylene glycol 2000 - 10% 38e PEGStearate - 35%/CMC (MV) - 5%/PLU L-121 - >30 5%/TOC - 5%/HA/β-TCP - 50%38f PEG Stearate - 35%/CMC (MV) - 5%/ >60 PLU L-121 - 10%/Polypropyleneglycol 2000 - 10%/HA/β-TCP - 40% 38g PLU F-127 - 60%/PLU L-121 -30%/ >60 HA/β-TCP - 10% 38h PLU F-127 - 60%/PLU P-123 - 40% <90 PWSFormulation 38i PLU P-123 - 45%/CHOL - 55% >60

Example 7

A rabbit bone implantation study was conducted to evaluate the in vivoabsorption of WSH-1.

The study involved New Zealand White Rabbits with defect sites locatedin the right and left femur diaphyses, measuring approximately 3 mm indiameter and full thickness in depth. At the desired endpoints animalswere sacrificed and the implant sites were excised for histopathology.The tissue explants were fixed, decalcified and embedded in paraffinprior to sectioning and staining with hematoxylin and eosin. Thepresence of residual implant material was defined as the actualobservation of material or voids where material had washed out duringprocessing. The amount of material was assessed using the followingscoring system:

-   -   0=No test article present (no residual material)    -   1=Trace amounts left; ˜¼ or less residual material remaining        (25% or less)    -   2=Small amount; ˜½ or less residual material remaining (less        than 50%)    -   3=Large amount; more than ½ residual material remaining (more        than 50% to 100%)

The test article was substantially absorbed by 8 days.

Equivalents

Those skilled in the art will recognize or be able to ascertain using nomore than routine experimentation, many equivalents to the specificembodiments of the invention. described herein. Such equivalents areintended to be encompassed by the following claims.

All references cited herein are incorporated herein by reference intheir entirety and for all purposes to the same extent as if eachindividual publication or patent or patent application was specificallyand individually indicated to be incorporated by reference in itsentirety for all purposes.

The present invention is not to be limited in scope by the specificembodiments described herein. Indeed, various modifications of theinvention in addition to those described herein will become apparent tothose skilled in the art from the foregoing description and accompanyingfigures. Such modifications are intended to fall within the scope of theappended claims.

1.-11. (canceled)
 12. A hand-moldable hemostatic composition having theconsistency of a putty, wherein the composition is effective fortamponade hemostasis of a bone or cartilage comprising: a. awater-soluble ethoxylated fatty acid; b. a freely water soluble (FWS)non-particulate solid base material comprising: i) block copolymers ofethylene and propylene oxide and ii) polypropylene glycol, wherein thecomposition further comprises a particulate material embedded within theFWS solid base material; and c. a water absorbing dissolution retardantthat increases the dissolution time of the FWS non-particulate solidbase material selected from the group consisting of substitutedpolysaccharides; sodium, potassium, and lithium salts of carboxymethylcellulose; starch glycolates; chitosan hydrochloride; hydroxylethylcellulose; hydroxypropylmethylcellulose; and sodium alginate, whereinthe composition has sufficient strength to adhere directly to the moistsurfaces of bleeding bone or cartilage, thereby creating a staticinterface that allows blood clotting to occur.
 13. The composition ofclaim 12, wherein the particulate material is absorbable, nonabsorbale,resorbable, or a mixture thereof.
 14. The composition of claim 13,wherein the absorbable material comprises a particulate ceramic or glassmaterial.
 15. The composition of claim 14, wherein the particulateceramic or glass material is selected from the group consisting ofsubstituted calcium phosphates; glass; calcium sulfate; calciumphosphosilicate; sodium phosphate; calcium aluminate; bone or a bonesubstitute; calcium phosphate; tricalcium phosphate; tetracalciumphosphate; dicalcium phosphate; calcium pyrophosphate; hydroxyapatite;biphasic calcium phosphates; hydroxyapatite and TCP containing calciumphosphates; multiphasic calcium phosphates; highly porousnanocrystalline hydroxyapatite (HA) in the presence of nanoporous silica(Si0₂); glass-ionomer, absorbable phosphate glass; an osteoconductiveplastic, polymer or polyurethane; and combinations thereof.
 16. Thecomposition of claim 15, wherein the substituted calcium phosphatescomprise a silica, strontium or magnesium calcium salt substitution. 17.The composition of claim 15, wherein the glass is a bioglass.
 18. Thecomposition of claim 12, wherein the composition optionally comprises atocopherol acetate.
 19. The composition of claim 12, wherein thecomposition further comprises one or more agents selected from the groupconsisting of an antimicrobial agent, an anesthetic, an analgesic, anantioxidant, a bone growth stimulating agent, an anti-inflammatoryagent, an osteoconductive agent, an osteoconductive component, a peptidegrowth factor, a chemotherapeutic agent, a softening agent, a chelatingor sequestering agent, a radiotransparent agent, a radiopaque agent, andan anti-adhesion agent.